Injectable thermoresponsive polyelectrolytes

ABSTRACT

Provided herein are compositions, devices, and systems comprising thermoresponsive, biodegradable elastomeric materials, and methods of use and manufacture thereof.

CROSS REFERENCE TO RELATED APPLICATIONS

This application is a divisional of Ser. No. 13/982,980, filed Oct. 14,2013, now allowed, which is a national phase application under 35 U.S.C.§ 371 of PCT International Application No. PCT/US2012/023293, filed Jan.31, 2012, which claims the benefit of and priority to U.S. ProvisionalApplication No. 61/438,071, filed on Jan. 31, 2011, each of which ishereby incorporated by reference in its entirety.

FIELD

Provided herein are compositions, devices, and systems comprisingthermoresponsive, biodegradable elastomeric materials, and methods ofuse and manufacture thereof.

BACKGROUND

Two- and three-dimensional polymer/hydrogel matrices provide a diversescaffold that can be modified and refined for various purposes.Hydrogels can be applied to various medical, engineering, biological andchemical applications, such as drug or chemical delivery, tissueengineering, cell transplantation, wound healing and rheologymodification (See, e.g.: Wu et al. (U.S. Pat. No. 6,030,634); Trollsaset al. (U.S. Pat. No. 6,458,889); Sehl et al. (U.S. Pat. No. 6,833,408);Stile & Healy (Biomacromolecules, 2001, 2(1): 185-194); Kim & Healy(Biomacromolecules, 2003, 4(5): 1214-1223); Li et al. (Biomaterials,2005, 26: 3093-3104); Rosenblatt et al. (U.S. Pat. No. 5,807,581);Ulbrich et al. (U.S. Pat. No. 5,124,421); Lee & Vernon (Macromol.Biosci. 2005, 5(7):629-635); Cha et al. (U.S. Pat. No. 5,702,717); Jeonget al. (U.S. Pat. No. 6,841,617); each of which is herein incorporatedby reference in its entirety).

Various kinds of thermoresponsive N-isopropylacrylamide (NIPA)copolymers are among an important class of bioengineering materials thathave been the subject of many extensive investigations in the field ofmodern macromolecular bioengineering and biotechnology (See, e.g.: MonjiN, Hoffman A S. Appl Biochem Biotechnol 1987; 14:107-20; Chen J-P,Hoffman A S. Biomaterials 1990; 11:631-4; Kim M R, Jeong J H, Park T G.Biotechnol Prog 2002; 18:495-500; Strauss U P, Schlesinger M S. J PhysChem 1978; 82:1627-32; Katre N V. Adv Drug Delivery Rev 1993; 10:91-114;Delgado C, Francis G E, Fisher D. Crit Rev Therapeut Drug Carrier Syst1992; 9:249-304; Kesim H, Rzaev ZMO, Dincer S, Piskin E. Polymer 2003;44:2897-909; Dincer S., Koseli, V., Kesim H., Rzaev ZMO, Piskin E. EurPolym J 2002; 38:43-52; Bulmus V. Patir S, Tuncel A, Piskin E. J ControlRelease 2001; 76:265-74; Lee B H, Vernon B. Macromol Biosci 2005;5:629-635; Guan J, Hong Y, Ma Z, Wagner W R. Biomacromolecules 2008;9:1283-1292.; Wang T, Wu D, Jiang X, Li X, Zhang J, Zheng Z, Zhuo R,Jiang H, Huang C. Eur J Heart Fail 2009; 11:14-19; Fujimoto K L, Ma Z,Nelson D M, Hashizume R, Guan J, Tobita K, Wagner W R. Biomaterials2009; 30:4357-4368; Yang J, Webb J A, Ameer G A. Adv Mater 2004;16:511-516; Yang J, Webb A, Pickerill S. Hageman G, Ameer G A.Biomaterials 2006; 27:1889-1898; herein incorporated by reference intheir entireties).

PEG is commonly incorporated into medical implants to resist proteinadsorption, platelet adhesion, and bacterial adhesion (Deible C R,Beckman E J, Russell A J, Wagner W R. J Biomed Mater Res 1998;41:251-256; Han D K, Park ICD, Hubbell J A, Kim Y H. J Biomater SciPolym Ed 1998; 9:667-680; Park K D, Kim Y S, Han D K, Kim Y H, Lee E H,Suh H, Choi K S. Biomaterials 1998; 19:851-859; Suggs L T, West J L,Mikos A G. Biomaterials 1999; 20:683-690; herein incorporated byreference in their entireties). Various copolymerization methods (ZakirM. O. Rzaev, Sevil Dincer, Erhan P. Prog Polym Sci 2007; 32:534-59) havebeen developed to synthesize the double double hydrophilic copolymerssuch as PEG-b-PNIPA (Zhu P W, Napper D R Macromolecules 1999;32:2068-2070; Zhu P W, Napper D H. Langmuir 2000; 16:8543-8545; Zhang WQ, Shi L Q, Wu K, An Y L. Macromolecules 2005; 38:5743-5747; hereinincorporated by reference in their entireties) or PEG-g-PNIPA (Qiu X, WuC. Macromolecules 1997; 30:7921-7926; Virtanen J, Baron C, Tenhu H.Macromolecules 2000; 33:336-341; herein incorporated by reference intheir entireties) by modifying PEG end-groups such as PEG-Br oramino-terminated PEG as macroinitiator or PEO methacrylate asmacromonomer. The solubilizing effect of PEG on the shrinking backbonecan compete with hydrophobic interactions in poly(NIPA) due todehydration at a temperature above 35° C. (Bar A, Ramon O, Cohen Y,Mizrahi S. J Food Eng 2002; 55:193-199).

Thermoresponsive materials such as PNIPAM-derivatized gelatin(PNIPAM-gelatin) (Matsuda T. Jpn J Artif Organs 1999; 28:242-245) andPNIPA-derivatized hyaluronic acid (PNIPAM-HA) (Ohya S, Nakayama Y,Matsuda T. Jpn J Artif Organs 2000; 29:446-451; herein incorporated byreference in its entirety) have been functioned as cell-adhesive andcell non-adhesive matrix to encapsulate bovine smooth muscle cells forcell therapies; however, the entrapped cells died in hydrogel (Ohya,Nakayama, Matsuda. J Artif Organs 2001; 4:308-314; herein incorporatedby reference in its entirety).

SUMMARY

Provided herein are thermoresponsive and biodegradable elastomericmaterials, including copolymers and compositions and structures, such ashydrogels, comprising the copolymers. The copolymers remain fluid at andbelow room temperature, solidify at physiological temperature, and bindto biological molecules. The copolymers also degrade and dissolve atphysiological conditions in a time-dependent manner, which may beimportant for removal of the hydrogel, for example, after an appliedsurgical or medical procedure. In some embodiments, copolymers describedherein and their degradation products are biocompatible, for example andwithout limitation, they are not cytotoxic.

According to one embodiment, copolymers comprise anN-isopropylacrylamide residue (an N-isopropylacrylamide monomerincorporated into a polymer), a citric acid residue, a polyethyleneglycol, and a multifunctional linker. The copolymer comprises apolyester linkage in its backbone. According to one non-limitingembodiment, the copolymer is prepared from at least five components:N-isopropylacrylamide or an N-alkyl acrylamide in which the alkyl ismethyl, ethyl, propyl, isopropyl or cyclopropyl, citric acid, apolyethylene glycol, and a multifunctional linker. In some embodiments,a copolymer comprises 2 or more (e.g., 2, 3, 4, 5) of:N-isopropylacrylamide or an N-alkyl acrylamide in which the alkyl ismethyl, ethyl, propyl, isopropyl or cyclopropyl, citric acid, apolyethylene glycol, and a multifunctional linker. Copolymers of thepresent invention are not limited by these components, and may comprisedifferent and/or additional components within the scope of theinvention. In certain embodiments, the copolymer is prepared bypolymerizing the N-alkyl acrylamide with a polyester macromer. Inspecific embodiments, the polyester macromer is apolycitrate-co-polyethylene glycol macromer, comprising glycerol1,3-diglycerolate diacrylate residues and varying numbers of citric acidand polyethylene glycol units/residues. Typically, each componentcontributes to the desired physical properties of the hydrogel to enablean injectable material for delivering drugs or chemicals, encapsulatingand transplanting cells, and injecting into empty cavities for wounds ortissue repair. In some embodiments, the citric acid component of thecopolymer binds to positively charged compounds including biomoleculessuch as protamine sulfate and/or other bioactive or biocompatiblematerials or factors. In certain embodiments, the composition of eachcomponent in the hydrogel determines the lower critical solutiontemperature (LCST) of the hydrogel. At a temperature less than the LCST,the hydrogel flows easily and can be injected into the desired shape.When the temperature is increased above the LCST, the hydrogelsolidifies and retains the shape. Once solidified, the hydrogel ishighly flexible and relatively strong at physiological temperature.

According to one embodiment, the polyester component within the macromerintroduces the degradability and hydrophilicity of the copolymer. Forcomplete removal of the copolymer, the copolymer includeshydrolytically-cleavable bonds that results in soluble, non-toxicby-products, even above the LCST of the non-degraded copolymer. In oneembodiment, the copolymer has a lower critical solution temperaturebelow 37° C. and, in particular embodiments, between 30° C. and 35° C.

Positively charged biomolecules or other compounds, such as proteins,carbohydrates, glycoproteins, etc. can be incorporated into thecopolymer through ionic interactions with the negatively chargedcarboxylate groups. In certain embodiments, protamine sulfate is asuitable compound, for instance and without limitation, about 10 mg/mlprotamine sulfate. In certain embodiments the protamine sulfate isN-diazeniumdiolated.

A composition comprising the copolymer described herein and an aqueoussolvent, for example and without limitation, water, saline andphosphate-buffered saline also is provided. In some embodiments,compositions also include an active agent, such as, without limitation,one or more of an antiseptic, an antibiotic, an analgesic, ananesthetic, a chemotherapeutic agent, a clotting agent, ananti-inflammatory agent, a metabolite, a cytokine, a chemoattractant, ahormone, a steroid, a protein and a nucleic acid. In one embodiment,where the composition comprises a clotting agent, one example of aclotting agent is desmopressin. A biological material, such as a cell ora virus particle may also be incorporated into the composition.

A method is provided of making a thermosensitive copolymer, for example,a co-polymer described herein, the method comprising co-polymerizingN-isopropylacrylamide with a citric acid-co-polyethylene glycolprepolymer further comprising glycerol 1,3-diglycerolate diacrylate.

The citric acid-co-polyethylene glycol prepolymer can be prepared by anyuseful method, for example and without limitation by step growthpolymerization. In order to prepare the copolymer of the presentinvention, it is useful to incorporate a multi-functional linker intothe prepolymer. In some embodiments, glycerol 1,3-diglycerolatediacrylate is used. Different feed ratios of citric acid, polyethyleneglycol, and glycerol 1,3-diglycerolate diacrylate can be used. In oneembodiment a molar ratio of 1:1.8:0.2 is used.

The N-isopropylacrylamide and poly (citric acid-co-polyethylene glycol)prepolymer can be co-polymerized by any useful polymerization method,for example and without limitation by free-radical polymerization.Various feed ratios of the poly (citric acid-co-polyethylene glycol)prepolymer and N-isopropylacrylamide can be used. For example butwithout limitation, the ratio of poly (citric acid-co-polyethyleneglycol) prepolymer and N-isopropylacrylamide (wt:wt) can be 5:95, 10:90,15:85, 20:80, 25:75, 30:70, 35:65, 40:60, 45:55, 50:50, 55:45, 60:40,65:35, 70:30, 75:25, 80:20, 85:15, 90:10, or 95:5. In certainembodiments, the ratio is 25:75, 50:50, or 75:25. In the particularembodiments, the feed ratio is 50:50.

According to another embodiment a method of growing cells is provided,comprising introducing cells into a copolymer composition describedherein to produce a cell construct and incubating the cell constructunder conditions suitable for growth of the cells. The composition cancomprise cell growth media to facilitate cell growth within thecomposition. The cell construct can be administered to a patient (placedin a patient's body at a desired location), such as a human patient. Inanother embodiment, the composition is administered to a patient withoutcells, but so that the patient's cells migrate into the composition. Thecomposition can be administered by a subcutaneous injection into thedesired site within the patient. To facilitate this, the composition maycomprise one or more of a cytokine, a cell growth or differentiationagent and a metabolite. The composition also may include an activeagent, such as, without limitation, an antiseptic, an analgesic, ananesthetic and an antibiotic. As above, the copolymer can be complexedwith protamine sulfate and/or N-diazeniumdiolated protamine sulfate, forexample and without limitation, at about 10 mg/ml.

In some embodiments, the present invention provides copolymerscomprising: (a) an N-alkyl acrylamide residue; and (b) a polyester. Insome embodiments, the polyester comprises one or more (e.g., each of):citric acid, polyethylene glycol, and glycerol 1,3-diglycerolatediacrylate. In some embodiments, the alkyl is selected from: methyl,ethyl, propyl, isopropyl and cyclopropyl. In some embodiments, theN-alkyl acrylamide residue comprises N-isopropylacrylamide. In someembodiments, the polyester consists of: citric acid, polyethyleneglycol, and glycerol 1,3-diglycerolate diacrylate. In some embodiments,the copolymer has a lower critical solution temperature below 37° C. Insome embodiments, the copolymer has a lower critical solutiontemperature of between 30° C. and 35° C. In some embodiments, thepresent invention provides a positively charged compound complexed tothe copolymer. In some embodiments, the positively charged compound isprotamine sulfate. In some embodiments, the positively charged compoundis diazeniumdiolated. In some embodiments, the composition furthercomprises one or more active agents selected from: an antiseptic, anantibiotic, an analgesic, an anesthetic, a chemotherapeutic agent, aclotting agent, an anti-inflammatory agent, a metabolite, a cytokine, achemoattractant, a hormone, a steroid, a protein, and a nucleic acid. Insome embodiments, the composition further comprises one or morebiological materials selected from a cell, a protein or a virus.

In some embodiments, methods are provided for manufacture of athermosensitive copolymer comprising co-polymerizing an N-alkylacrylamide in which the alkyl is one of methyl, ethyl, propyl, isopropyland cyclopropyl; and a polyester comprising citric acid, polyethyleneglycol, and glycerol 1,3-diglycerolate diacrylate. In some embodiments,the N-alkyl acrylamide is N-isopropylacrylamide. In some embodiments,the monomers are co-polymerized by free-radical polymerization.

In some embodiments, methods are provided for growing cells, comprisingintroducing cells into a copolymer of the present invention to produce acell construct and incubating the culturing mixture under conditionssuitable for growth of the cells. In some embodiments, cell growth mediais provided. In some embodiments, methods further comprise administeringthe cell construct into a patient. In some embodiments, the patient is ahuman patient. In some embodiments, the composition is administered to apatient and patient's cells migrate into the composition. In someembodiments, the composition comprises one or more of a cytokine, a cellgrowth or differentiation agent and a metabolite. In some embodiments,the composition comprises one or more of an antiseptic, an analgesic, ananesthetic and an antibiotic.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 shows the chemical structure of the multi-functional linkerglycerol 1,3-diglycerol diacrylate.

FIG. 2 is a schematic of the synthesis of poly (citricacid-co-PEG-co-NIPAM) copolymer.

FIG. 3 shows the ¹H NMR spectrum of the CPN55 copolymer is a schematicshowing the diazeniumdiolation of protamine sulfate in room temperature(RT) under NO gas of 5 atm.

FIG. 4 shows phase transition curves of CPEGD prepolymer, PNIPAMhomopolymer, CPN55 copolymer and the mixture of CPEGD and PNIPAM inaqueous solution as measured using a Jasco-815 CD spectrophotometer at550 nm.

FIG. 5 shows phase transition curves of PNIPAM homopolymer and CPNcopolymers with different ratios CPEGD and PNIPAM in aqueous solution asmeasured using compositions in aqueous solution as measured using aJasco-815 CD spectrophotometer at 550 nm.

FIG. 6 shows the pH of the CPEGD prepolymer and CPN55 polyelectrolyte inaqueous solution with increasing concentrations.

FIG. 7 is a schematic of the diazeniumdiolation of protamine sulfate atroom temperature under 5 atm. NO gas.

FIG. 8 shows the UV-VIS spectrum of N-Diazeniumdiolated protaminesulfate at 37° C. in PBS over time. The spectrum was taken with a freshsample and then again after 15 minutes, 30 minutes, 1 hour, 2 hours, 4hours, 8 hours, 24 hours, and 48 hours incubation in PBS at 37° C. Thepeak at 254 nm disappeared gradually over time following first-orderkinetics.

FIG. 9 shows the Proton NMR spectra of protamine sulfate (PS) before andafter NO loading.

FIG. 10 shows the release of NO from PNIPAM homopolymer, the mixture ofCPEGD and PNIPAM, and CPN 55 with PSNO at different times (mean+/−SD;n=3).

FIG. 11 shows NO release over time from CPN55:PSNO complexes prepared atconcentrations of 70 mg/ml, 100 mg/ml, 130 mg/ml, and 160 mg/ml CPN55(mean+/−SD; n=3).

DETAILED DESCRIPTION

According to embodiments of the compounds and compositions describedherein, provided herein are injectable hydrogels that are biodegradable,elastomeric and thermoresponsive and which can easily take the shape ofa cavity into which they are injected in advance of phase transition tosolid. Biocompatible copolymers and compositions comprising suchcopolymers are provided. In certain embodiments, the copolymers anddegradation products thereof are non-toxic and typically have an LCSTbetween room temperature and 37° C. so that they are liquid at roomtemperature and gelled at 37° C. which facilitates their use in humans,for example for wound treatment and as a cellular growth matrix orniche. In some embodiments, the copolymers are injectable as a liquid ator below room temperature (about or exactly 25° C.) and are solid atbody temperature (about or exactly 37° C.). These materials are usefulfor a number of purposes. For example, in treatment of patients, theymay be used as an injectable stem cell niche for bone marrow transplantsor for other transplantation settings; delivery vehicles forchemotherapy to tissue, such as, for example and without limitation, gutfollowing tumor resections; sealants for pulmonary and neuralapplications as well as for emergency treatment of wounds. The materialsalso can find use as bulking agents for cosmetic applications or, evenmore generally, rheology modifiers. The copolymer comprises numerousester linkages in its backbone so that the copolymers are erodible insitu. Certain degradation products of the polymer are soluble andnon-toxic. In particular embodiments, the copolymer is amine-reactive sothat it can conjugate with proteins, such as collagen. Activeingredients, such as drugs, can be incorporated into compositionscomprising the copolymer.

In some embodiments, synthesized biodegradable thermoresponsivepolyanions described herein are quickly solidified at 37° C. containingthe media without shrinkage and conveniently implanted by injection inaqueous solution. The thermoresponsive polyelectrolyte with carboxylicgroups complexes with cationic protein such as protamine sulfate orprotein NO donor such as N-diazeniumdiolated protamine sulfate forcontrolled NO release.

According to certain embodiments, copolymers comprise four types ofsubunits/residues: 1) N-alkyl acrylamide in which the alkyl maycomprise, but is not limited to: methyl, ethyl, propyl, isopropyl orcyclopropyl, for example N-isopropylacrylamide, as a thermosensitivecomponent after polymerization; 2) citric acid 3) polyethylene glycolfor improvement of hydrophilicity and 4) a multifunctional linker. Insome embodiments, copolymers comprise 1, 2, or 3, of the above fourtypes or subunits/residues alone or with additional types ofsubunits/residues.

The copolymers, compositions and components thereof are preferablybiocompatible. By “biocompatible,” it is meant that a polymercomposition and its normal in vivo degradation products arecytocompatible and are substantially non-toxic and non-carcinogenic in apatient within useful, practical and/or acceptable tolerances. By“cytocompatible,” it is meant that the copolymers or compositions aresubstantially non-toxic to cells and typically and most desirably cansustain a population of cells and/or the polymer compositions, devices,copolymers, and degradation products thereof are not cytotoxic and/orcarcinogenic within useful, practical and/or acceptable tolerances. Forexample, a copolymer composition when placed in a human epithelial cellculture does not adversely affect the viability, growth, adhesion, andnumber of cells. In one non-limiting example, the co-polymers,compositions, and/or devices are “biocompatible” to the extent they areacceptable for use in a human or veterinary patient according toapplicable regulatory standards in a given legal jurisdiction. Inanother example the biocompatible polymer, when implanted in a patient,does not cause a substantial adverse reaction or substantial harm tocells and tissues in the body, for instance, the polymer composition ordevice does not cause necrosis or an infection resulting in harm totissues organs or the organism from the implanted compositions.

As used herein, a “polymer” is a compound formed by the covalent joiningof smaller molecules, which are referred to herein as residues, orpolymer subunits, when incorporated into a polymer. A “copolymer” is apolymer comprising two or more different residues. Prior toincorporation into a polymer, the residues typically are described asmonomers. Non-limiting examples of monomers, in the context of thecopolymer described herein, include: citric acid monomers, polyethyleneglycol monomers, glycerol 1,3-diglycerolate diacrylate monomers, andN-alkyl acrylamide monomers. A monomer may be a macromer prepared fromeven smaller monomers, such as the polyethylene glycol macromerdescribed herein. Polyester polymer backbones are polymer backbonescontaining two or more ester groups. A polyester linkage has an averageof more than one ester units (—C(O)O—), as opposed to an ester linkagethat has one ester unit. An example is a poly (citricacid—co-polyethylene glycol prepolymer as described herein.

Lower critical solution temperature (LCST) refers to the temperaturebelow which the constituents of the hydrogel are soluble in water andabove which the constituents are insoluble. When the LCST is reached,the polymer constituents in an aqueous solution will aggregate to formhydrogel. The LCST can be determined by measuring the change intransmittance with a UV-Vis spectrometer as a function of temperature(Advanced Drug Delivery Reviews (1998), 31: 197-221 and Annals N.Y. ofScience, 1999, 875(1):24-35). LCST also can be determined by any otheruseful method—for example and without limitation by DifferentialScanning Calorimetry. UV-Vis spectroscopy is used to measure LCTS in theexamples below.

One aspect of the polymers described herein is that the LCST of thesepolymers is typically between 18° C. and about 37° C. so that thepolymer can be distributed through the marketplace, stored andadministered to a patient as a liquid at ambient temperatures (or, ifnecessary, maintained at a cool temperature with an ice-pack,refrigerator or other cooling device), and the polymer then gels as itwarms past its LCST. Many polymers suitable for administration topatients require mixing of monomers immediately prior to use, which isundesirable for many reasons. For instance, it is impractical to askdoctors, nurses or technicians to mix monomers as they need the polymer.Further, monomers can have varying degrees of toxicity. The copolymersdescribed herein do not require conducting a chemical reaction at thesite of use and the copolymers can be washed free of monomercontamination prior to distribution in the marketplace. Lastly, therelease of a portion of the aqueous phase during phase transition canfacilitate local drug delivery in the excluded aqueous phase.

Another desirable physical quality of the polymers described herein isthat, when ester linkages in the backbone are hydrolyzed (for instanceover time in situ in a living system, such as a human patient), thereleased copolymer fragments are soluble (and as an additional benefit,non-toxic), facilitating safe degradation and clearance of the polymerover time in a living system such as a human body.

In one embodiment of the copolymer useful in humans or animals, thecopolymer has a lower critical solution temperature below 37° C. Forveterinary applications, the LCST can be slightly higher as the corebody temperature of certain animals (e.g., cats, dogs, horses, cows,sheep and goats) is in the range of 38° C.−39° C.

In some medical or veterinary uses, the copolymers and compositionscomprising the copolymers serve as adhesives or fillers. They may beapplied to wounds or into body cavities or used as a tissue packing toapply compression. As such, embodiments of the copolymer solutionsdescribed herein are applied to wounds. In some embodiments, copolymersare applied with a warming compress, “heat pack,” or other suitablemeans to ensure that the copolymer is maintained at a temperature aboveits LCST and thus remains gelled when in contact with any cooler areasof the body, typically the skin. As a hydrogel, embodiments of thecopolymers disclosed herein may be contained in a composition comprisingthe copolymer and an aqueous solution that does not interferesubstantially with the LCST and polymer structure in its intended use.For instance, in certain embodiments, the composition comprises anyaqueous solvent, optionally pharmaceutically acceptable, including,without limitation, water, PBS, Saline, etc. As used herein, and“aqueous solvent”, is an aqueous solution compatible with the copolymerwhich can be absorbed into the copolymer matrix. In some embodiments,the composition also comprises an active agent, biological or drug, suchas, without limitation: antibiotics, clotting agents (withoutlimitation, an antifibrinolytic, such as desmopressin/DDVAP),analgesics, anesthetics, antiseptics, anti-inflammatory agents,chemotherapeutic agents, metabolites, rheology modifiers, cytokines,chemoattractants, hormones, steroids, proteins (including enzymes),nucleic acids, cells, virus particles, nucleic acids, biomatrices orprecursors thereof, or a foaming agent. In one embodiment, thecomposition comprises stem cells (such as adipose-derived stem cells) orother progenitor cells so that the composition is useful as abiodegradable tissue engineering scaffold. The composition, even withoutcells, is useful as a cell growth niche or scaffolding into which cellssuch as native stem/progenitor cells can migrate in situ. In such anembodiment, chemokines, cellular growth agents and cellulardifferentiation agents can be included within the composition to attractcells into the composition and promote cellular growth anddifferentiation when placed in situ.

According to particular embodiments, in its application to woundtreatment, a clotting agent such as desmopressin is included in apolymer composition. An appropriate, e.g., pharmaceutically acceptable,foaming agent as are well-known in the relevant arts also may beincluded for the purpose of creating compression in a wound, whetherexposed to a body surface in the case of (for example) puncture woundsor bullet wounds, or internal wounds, in which case, the polymer can beinjected into or near a site of internal bleeding. As such, compositionsfind use in many situations, ranging from home use to stabilization ofbleeding or massively bleeding patients in emergency and battlefieldsituations. In some embodiments, copolymers also find use duringsurgical procedures to apply compression and otherwise secure a site ofinjury, such as a portion of a patient's intestine, nasal passage orsinus cavity where a tumor or polyp has been removed or after othersurgeries. The benefits of such a reversibly-gelling copolymercomposition is that the composition can be removed simply by cooling,for example and without limitation, by flushing with cool (lower thanthe copolymer's LCST) flushing solution, such as water, saline orphosphate-buffered saline. Thus, while a wound and bleeding in a patientcan be stabilized by application of the polymer, the polymer can beselectively eroded in an emergency room or during surgery simply byflushing with a cool (for example and without limitation, 0° C. to 30°C.) saline solution.

The properties of the hydrogels can be modulated, for example, byvarying the feed ratios of the monomers during the synthesis of theCPEGD prepolymer, by varying the feed ratios of the CPEGD prepolymer andthe NIPAM during the synthesis of the poly (citric acid-co-polyethyleneglycol-N-isopropylacrylamide) copolymer, or by varying the concentrationof the poly (citric acid-co-polyethylene glycol-N-isopropylacrylamide)copolymer prior to gel formation. In certain embodiments, theconcentration of the copolymer is between 1 mg/ml and 250 mg/ml. Inparticular embodiments, the concentration of the copolymer is 40 mg/ml,50 mg/ml, 60 mg/ml, 70 mg/ml, 80 mg/ml, 90 mg/ml, 100 mg/ml, 110 mg/ml,120 mg/ml, 130 mg/ml, 140 mg/ml, 150 mg/ml, or 160 mg/ml. In someembodiments, the concentration of the copolymer is between 50 mg/ml and100 mg/ml.

In a further embodiment, the composition serves as a cell growth medium.According to one embodiment, cells are introduced into a compositioncomprising a copolymer as described herein to produce a cell construct.The cell construct is incubated under conditions suitable for growth ofthe cells. That is, the cell construct can be placed in an incubator orinto a patient so that the cells are maintained under adequateenvironmental conditions to permit the cells to survive, proliferate,differentiate and/or express certain products. “Cell growth” means thatthe cells survive and preferably, though not exclusively, divide andmultiply. The composition may comprise cell growth media, whichtypically provides necessary nutrients and environmental conditions forcell growth. The cells may be introduced and incubated under conditionssuitable for cell growth by introducing the composition into a patientand allowing native cells, such as stem cells to migrate into thecomposition. The composition can be administered by injecting thecomposition into the region requiring cellular growth or remodeling,such as a region of damaged tissue. In one non-limiting example, thedamaged tissue is within the cardiac wall caused by a myocardialinfarction and the composition is injected into the cardiac wall. In onevariation of that embodiment, cytokines, chemoattractants, nutrientsand/or cell differentiation factors are included in the composition. Thecomposition may also contain one or more of an antiseptic, an analgesic,an anesthetic and an antibiotic (for example, for selection of the cellsor to prevent bacterial growth in the composition).

In another aspect, this invention provides a facilitation of localdelivery of nitric oxide (NO) and protamine (sulfate), for suppressionof platelet aggregation/adhesion and proliferation of smooth musclecells. NO has drawn a great deal of attention from the researchcommunity to understand its synthesis cascade and regulatory functionsin vivo (Palmer, R. M. J.; Ashton, D. S.; Moncada, S., Nature 1988, 333,(6174), 664-666; Ignarro, L. J., Seminars in Hematology 1989, 26, (1),63-76; Hibbs, J. B., Research in Immunology 1991, 142, (7), 565-569;Garthwaite, J., Trends in Neurosciences 1991, 14, (2), 60-67; hereinincorporated by reference in their entireties). These findings arousedenormous efforts to develop NO-generating compounds such asN-diazeniumdiolates (Kaul, S.; Cercek, B.; Rengstrom, J.; Xu, X. P.;Molloy, M. D.; Dimayuga, P.; Parikh, A. K.; Fishbein, M. C.; Nilsson,J.; Rajavashisth, T. B., Journal of the American College of Cardiology2000, 35, (2), 493-501; Saavedra, J. E.; Southan, G. J.; Davies, K. M.;Lundell, A.; Markou, C.; Hanson, S. R.; Adrie, C.; Hurford, W. E.;Zapol, W. M.; Keefer, L. K., Journal of Medicinal Chemistry 1996, 39,(22), 4361-4365; Sogo, N.; Magid, K. S.; Shaw, C. A.; Webb, D. J.;Megson, I. L., Biochemical and Biophysical Research Communications 2000,279, (2), 412-419), nitrosothiols (Kharitonov, V. G.; Sundquist, A. R.;Sharma, V. S., Journal of Biological Chemistry 1995, 270, (47),28158-28164; Singh, R. J.; Hogg, N.; Joseph, J.; Kalyanaraman, B.,Journal of Biological Chemistry 1996, 271, (31), 18596-18603) andNO-metal complexes (Mitchell-Koch, J. T.; Reed, T. M.; Borovik, A. S.,Angewandte Chemie-International Edition 2004, 43, (21), 2806-2809; Xiao,B.; Wheatley, P. S.; Zhao, X. B.; Fletcher, A. J.; Fox, S.; Rossi, A.G.; Megson, I. L.; Bordiga, S.; Regli, L.; Thomas, K. M.; Morris, R. E.,Journal of the American Chemical Society 2007, 129, (5), 1203-1209;herein incorporated by reference in their entireties), with the aim oftaking advantage of NO as a potential therapeutic agent. The use ofmaterials described herein for local delivery of nitric oxide is highlydesirable for prosthetic bypass grafts, catheters, stents,intracorporeal sensors and other blood contacting objects. It has beenrevealed that NO is extensively implicated in diverse in vivo functionsin the human body, and considerable research has been devoted tosynthesis and modification of artificial compounds to bear NO donorcomplexes such as N-diazeniumdiolate, nitrosohydroxyamine ornitrosothiol groups, which moieties can instantaneously produce NO underphysiological conditions. Diazeniumdiolated protamine or protaminesulfate is thought to induce vasorelaxation and inhibition of smoothmuscle cell proliferation by the dual effect of exogenous NO deliveryand upregulation of endogenous NO production by vascular endothelialcells. The unique nature of protamine for endogenous NO induction makesthis system still effective for local NO generation even after depletionof the exogenous NO moieties. The diazeniumdiolatedprotamine-encapsulating, NO-releasing system can easily provide forincorporation with any type of medical device via surface coating orembedding. Protamine, an L-arginine-rich protein (Ando, T.; Yamasaki,M.; Suzuki, K., Molecular Biology, Biochemistry & Biophysics 1973, 12,1-114), has numerous guanidine groups that can potentially be convertedinto diazeniumdiolate moieties under highly pressurized NO atmosphere.Diazeniumdiolated compounds have been proven to dissociate and generateNO spontaneously upon proton contact, e.g. by placing the compound inphysiological fluids. On the other hand, protamine, probably as anexogenous source of (poly)-L-arginine (Lee, Y.; Yang, J.; Rudich, S. M.;Schreiner, R. J.; Meyerhoff, M. E., Analytical Chemistry 2004, 76, (3),545-551; herein incorporated by reference in its entirety), is expectedto serve to stimulate local NO production by acting with endothelialcells (Pevni, D.; Gurevich, J.; Frolkis, I.; Keren, G.; Shapira, I.;Paz, J.; Kramer, A.; Locker, C.; Mohr, R., The Annals of ThoracicSurgery 2000, 70, (6), 2050-2053; Evora, P. R.; Pearson, P. J.; Schaff,H. V., The Annals of Thoracic Surgery 1995, 60, (2), 405-410; Li, J. M.;Hajarizadeh, H.; La Rosa, C. A.; Rohrer, M. J.; Vander Salm, T. J.;Cutler, B. S., The Journal of Cardiovascular Surgery 1996, 37, (5),445-452; herein incorporated by reference in their entireties) andpossibly smooth muscle cells (Takakura, K.; Mizogami, M.; Fukuda, S.,Journal Canadien d′Anesthesie 2006, 53, (2), 162-167; hereinincorporated by reference in its entirety), thus leading toanti-thrombosis and vasorelaxation.

Compositions comprising one or more copolymers described herein can bedistributed for use in any suitable vessel. In one instance, thecomposition is packaged in a sealed container, from which thecomposition can be poured, squeezed or otherwise decanted, for exampleand without limitation, by use of a syringe. The vessel can be a bag,such as an IV bag. In another embodiment, the composition can bedistributed in a syringe for immediate dispensation into a wound or bodycavity/location. A syringe can be fitted with any type of needle, tip,tube, balloon device or other useful fitting for facilitating accurateplacement of the solution in or around a desired delivery site, forexample and without limitation, for delivery into the large intestine ofa patient after removal of a tumor. In another embodiment, thecomposition and a pharmaceutically acceptable solvent is stored within asyringe at or below 4° C. and the syringe is fitted with a needle gaugesufficient to allow for injection without increased pressure but alsoprohibit back flow of the solution into the syringe after injection,such as, without limitation, a 16 through 23 G (gauge) needle, and incertain embodiments an 18 G or 20 G needle. Thus, methods of useembodying the above-described uses for a copolymer described herein andcompositions comprising the copolymer are contemplated and embraced aspart of the present invention.

In another use, a composition described herein can be used for cosmeticpurposes, such as for a rheology modifier. Ingredients, includingwithout limitation colorants, fragrances, flavors, and other ingredientslisted herein, including active agents, may be included in thecomposition.

In some embodiments, kits and/or systems are provided comprising thecopolymers and/or compositions provided herein with additionalcompositions, reagents, instructions, containers, cells, controls,buffers, etc.

EXPERIMENTAL

The following examples are provided for illustration purposes and arenot intended to limit the scope of the present invention.

Example 1 Synthesis of Poly(Citric Acid-Co-Polyethylene Glycol) (CPEGD)Prepolymers

The general synthesis of citric acid-based prepolymers has beenpreviously described (Yang J, Webb J A, Ameer G A. Adv Mater 2004;16:511-516; Yang J, Webb A, Pickerill S. Hageman G, Ameer G A.Biomaterials 2006; 27:1889-1898; herein incorporated by reference in itsentirety). For example, citric acid (Sigma-Aldrich, 99.5+%), PEG (400,Aldrich) and glycerol 1,3-diglycerolate diacrylate (Aldrich) withdifferent feed molar ratios such as 1/1.8/0.2 were melted together at130° C. while stirring for 30 minutes to perform the step growthpolymerization. The structure of glycerol 1,3-diglycerolate diacrylateis shown in FIG. 1. The CPEGD prepolymers were obtained by lowering thereactive temperature to room temperature and directly used in thefollowing reaction without further purification.

Example 2 Synthesis of Poly(Citric Acid-Co-PEG-N-Isopropylacrylamide)(CPN) Copolymers

The synthetic scheme for the synthesis of CPN copolymers is shown inFIG. 2. N-Isopropylacrylamide (NIPAM, Aldrich 98%) was purified byrecrystallization from hexanes and dried under vacuum for 4 days, 2,2′-Azobisisobutyronitrile (AIBN, Aldrich 98%) was purified byrecrystallization from methanol. CPN copolymers with CPEGD/NIPAM feedratios (w/w) of 25/75, 50/50 and 75/25 were synthesized by radicalpolymerization in 1,4-dioxane at 70° C. with AIBN radical initiator atconstant total concentration of monomers under N₂. Briefly, the totalmonomer concentration was 2.78 mol/L in 1, 4-dioxane, and the AIBNconcentration was (6.5×10−3 mol/L). Appropriate quantities of monomers,1,4-dioxane and AIBN were placed into a standard pyrex-glass tube,nitrogen was bubbled through the solution at room temperature for 15 minprior to the addition of the initiator to reduce oxygen content in thepolymerization reaction. The copolymerization was conducted at 70° C.for 8 h under a nitrogen atmosphere. Subsequently, the copolymer wasprecipitated in an excess of diethyl ether, filtered, and then driedunder reduced pressure. The yield was around 86%.

The synthesis of thermoresponsive CPN polyelectrolytes was confirmed by¹H NMR (FIG. 3), which contained proton peaks in agreement with themolecular structure of CPN copolymers.

Example 3 Phase Transition and pH Change of Thermoresponsive CPNPolyelectrolytes

The phase transition of thermoresponsive CPN polyelectrolyte solutionsin water (10 wt %) were determined by measuring optical absorption at550 nm over a temperature range of 25 to 45° C. at a heating rate of 1°C./min. The onset temperature of transition curve of each copolymer wasseen as its lower critical solution temperature (LCST). The LCSTs ofPNIPA homopolymer, CPEGD prepolymer, the mixture of PNIPA and CPEGD havealso recorded as a comparison. The pH change of CPEGD prepolymers andCPN polyelectrolytes with different concentrations was measured using apH-meter.

As used herein, the term CPN55 refers to a poly(citricacid-co-PEG-N-isopropylacrylamide) copolymer prepared with a CPEGD/NIPAMfeed ratio (w/w) of 50:50. The term CPN75 refers to a poly(citricacid-co-PEG-N-isopropylacrylamide) copolymer prepared with a CPEGD/NIPAMfeed ratio (w/w) of 25:75. The obtained copolymers showed the phasetransition behavior between room temperature and body temperature. FIGS.4 and 5 illustrate the temperature-dependent turbidity-concentrationrelationship. The CPEGD prepolymer did not show a phase transition,compared with the mixture of CPEGD prepolymer and PNIPAM homopolymer.CPN55 and CPN75 polyelectrolytes exhibited sharp thermo-precipitation atabout 33° C. and 32° C. respectively, which are their lower criticalsolution temperatures (LCST). With the increasing content of PEG, theLCSTs of CPN polyelectrolytes decreased. In particular, the CPN55polyelectrolyte at a concentration of 40 mg/ml reversibly and quicklyformed a solid at 37° C.

CPEGD prepolymers synthesized by step growth polymerization exhibitedunreacted carboxylic groups due to the tri-functional species of citricacid such that the CPN copolymer was essentially a polyelectrolyte ofnegative charge. The pH of CPN55 polyelectrolyte at 10 mg/ml was3.02+0.3 in aqueous solution and 5.21±0.5 in PBS buffer. With theincreasing concentrations of CPN55 polyelectrolyte in PBS solution, thepolyelectrolyte exhibited more acidity as shown in FIG. 6.

Example 4 Biodegradation of Thermoresponsive CPN Polyelectrolytes

Thermoresponsive CPN polyelectrolytes with different concentrations wereproduced in PBS buffer at room temperature, and solidified at 37° C.These samples with 2 ml PBS (pH=7.4) buffer on the top were incubated at37° C., then the media were removed and mass losses of thesethermoresponsive CPN polyelectrolytes were measured in predefined timepoints after lyophilization to evaluate the degradation.

Thermoresponsive CPN polyelectrolytes with different concentrationsdegraded over time in PBS solution, and the mass loss increased with theincreasing H₂O content contained in the hydrogels in agreement withtheir corresponding concentrations.

Example 5 Release of Protamine and Nitric Oxide from ThermoresponsiveComplexes Diazeniumdiolation of Protamine Sulfate:

The synthetic scheme for the diazeniumdiolation of protamine sulfate isshown in FIG. 7. Protamine sulfate (PS) salt from salmon (Sigma,Milwaukee, Wis.) was used as an NO carrier due to the numerousguanidinium and secondary amide moieties in the macromolecular chainwhich can be functionalized to diazeniumdiolate groups.N-diazeniumdiolated protamine sulfate (PSNO) was obtained by NOtreatment of PS. 500 mg PS was dispersed into 10 mL of sodium methoxide(NaOMe), placed in a pressure bottle and treated with 5 atm pressurizedNO gas for three days. The resulting residue was vacuum-dried and storedin a vacuum desiccator, light-protected at room temperature.

After PS was treated with 5 atm pressurized NO-gas for 3 days in NaOMewith and without a solvent, a successful conversion of PS to an NO donor(PSNO) was achieved as indicated by the peak at 254 nm (FIG. 8). Thepeak gradually disappeared during the first 2 days following first-orderkinetics. Total nitrite content, equivalent to the NO released, wasmeasured in samples after 2 days. The total nitrite release that couldbe obtained from diazeniumdiolated PS was 201.8±3.7 μmol/g PS when NaOMewas used as the solvent, an approximately 500-fold increase inNO-loading when compared to solvent-free conversion of PS which was0.4±0.07 μmol/g PS. FIG. 9 shows the Proton NMR spectra of protaminesulfate (PS) before and after NO loading.

Release of NO and Protamine Sulfate from Thermoresponsive CPN Complexes:

Thermoresponsive CPN polyelectrolytes were dissolved into PBS buffers toform the solutions of different concentrations such as 40 mg/ml, 70mg/ml, 100 mg/ml, 130 mg/ml, 160 mg/ml. PS and PSNO were added into thepolyelectrolyte solutions to obtain 10 mg/ml PS solutions. NO release invitro was measured in a PBS solution at 37° C. At specific time pointssolutions were centrifuged, decanted and refilled with fresh PBS. Thedecanted solution was used to assess nitrite amounts by Griess assay.Briefly, 100 μl samples were pipetted into a 96-well microtiter plate,neutralized with 0.5M HCl, and chilled to 4° C. Then 40 μl of a 1:1mixture of 6M HCl and 12.5 mM sulfanilamide were added for 10 min at 4°C. 20 μl of 12.5 mM N-(naphthyl)-ethylenediamine dihydrochloride (NEDA)was then added to form an azo compound whose concentration is directlyproportional to the concentration of nitrite. After 15 min of incubationat room temperature, the concentration of the azo compound can bedetermined by its maximum absorbance at 540 nm as measured via aLabsystems Muhiskan RC 96-well microtiter plate reader. The measurementof nitrites as a direct stoichiometric derivative of NO is commonly usedfor NO release measurements. PS amounts were determined using a standardmicro-BCA assay, 100 μl samples were pipetted into a 96-well microtiterplate, then 100 μl of the Micro-BCA reagent mixture was added to eachwell and mixed thoroughly on a plate shaker for 30 seconds. The platewas covered using Sealing Tape for 6-Well Plates and incubated at 37° C.for about 2 hours. The plate was then cooled to room temperature and theabsorbance measured at or near 562 nm on a plate reader.

Results showed that all NO was released from the PNIPAM homopolymer andthe mixture of CPEGD and PNIPAM in less than 1 day (FIG. 10); however,the NO release from CPN55 complexes was strongly affected by theconcentration of the CPN55 complex. NO is released from CPN55 complexesof 40 mg/ml over up to 5 days and from CPN55 complexes of 100 mg/ml overup to 2 weeks. As shown in FIG. 11, CPN55 complexes of 160 mg/ml showedthe lowest release rate of NO. The release profiles indicated that NOrelease can be controlled by the concentration of CPN complexes in thesolution.

Example 6

Cytocompatibility of thermoresponsive CPN polyelectrolytes Human aorticsmooth muscle cells (HASMC) were cultured in a 250 ml culture flask withSmGM-2 medium (Clonetics, Walkersville, Md.) supplemented with insulin,human fibroblast growth factor-0 (hFGF-β), Gentamicin sulfateamphotericin B, fetal bovine serum (FBS) and human recombinant epidermalgrowth factor (hEGF). Upon 80-90% confluency, the cells were passaged orused for experiments. All the thermoresponsive polymer samples withdifferent concentrations in PBS buffer were sterilized under UV lightexposure overnight. For all the experiments, the cells were seeded into48 well plates (Falcon) at a density of 12,000 cells per well. Followingseeding, the cells were incubated with PNIPA of 20 mg/ml and 40 mg/mland CPN polyelectrolyte of 50 mg/ml and 100 mg/ml at 37° C. and 5% CO2in a humid environment for 1, 3, 5, or 7 days. The morphology ofattached cells was observed and recorded at 24 h after cell seeding withan inverted light microscope (Nikon Eclipse, TE2000-U) equipped with aPhotometrics CoolSNAP HQ (Silver Spring, Md.).

The solutions quickly gelled in several minutes, indicated that thecells were entrapped into CPN55 hydrogels which can effectivelyimmobilize cells and serve as extracellular matrix. The cells survivedand spread in the CPN55 gels after 7 days. The cell morphologies in CPNpolyelectrolytes of 50 mg/ml and 100 mg/ml indicated that cells cansurvive in the hydrogels and that the cells are retained longer when thegels are prepared at higher concentrations of polyelectrolyte.

We claim:
 1. A copolymer comprising: (a) an N-alkyl acrylamide residue;and (b) a polyester comprising: citric acid, polyethylene glycol, andglycerol 1,3-diglycerolate diacrylate.
 2. The copolymer of claim 1,wherein the alkyl is selected from: methyl, ethyl, propyl, isopropyl andcyclopropyl.
 3. The copolymer of claim 2, in which said N-alkylacrylamide residue comprises N-isopropylacrylamide.
 4. The copolymer ofclaim 1, wherein said polyester consists of: citric acid, polyethyleneglycol, and glycerol 1,3-diglycerolate diacrylate.
 5. The copolymer ofclaim 1, wherein the copolymer has a lower critical solution temperaturebelow 37° C.
 6. The copolymer of claim 1, wherein the copolymer has alower critical solution temperature of between 30° C. and 35° C.
 7. Thecopolymer of claim 1, further comprising a positively charged compoundcomplexed to the copolymer.
 8. The copolymer of claim 7, wherein thepositively charged compound is protamine sulfate.
 9. The copolymer ofclaim 8, wherein the protamine sulfate is diazeniumdiolated.
 10. Acomposition comprising the copolymer of claim 1, and an aqueous solvent.11. The composition of claim 10, further comprising one or more activeagents selected from: an antiseptic, an antibiotic, an analgesic, ananesthetic, a chemotherapeutic agent, a clotting agent, ananti-inflammatory agent, a metabolite, a cytokine, a chemoattractant, ahormone, a steroid, a protein, and a nucleic acid.
 12. The compositionof claim 10, further comprising one or more biological materialsselected from a cell, a protein or a virus.
 13. A method of making athermosensitive copolymer comprising co-polymerizing an N-alkylacrylamide in which the alkyl is one of methyl, ethyl, propyl, isopropyland cyclopropyl; and a polyester comprising citric acid, polyethyleneglycol, and glycerol 1,3-diglycerolate diacrylate.
 14. The method ofclaim 13, in which the N-alkyl acrylamide is N-isopropylacrylamide. 15.The method of claim 13, wherein the monomers are co-polymerized byfree-radical polymerization.
 16. The method of claim 13, wherein thefeed ratio of N-alkyl acrylamide to polyester is about 25:75 wt/wt. 17.The method of claim 13, wherein the feed ratio of N-alkyl acrylamide topolyester is about 50:50 wt/wt.
 18. The method of claim 14, wherein thefeed ratio of N-alkyl acrylamide to polyester copolymer is about 25:75wt/wt.
 19. A method of growing cells, comprising introducing cells intoa composition of claim 10 to produce a cell construct and incubating theculturing mixture under conditions suitable for growth of the cells. 20.The method of claim 20, wherein the composition is administered to apatient and patient's cells migrate into the composition.